Imaging apparatus

ABSTRACT

An imaging apparatus includes a planar image acquisition unit configured to acquire a planar image of a subject, a tomographic image acquisition unit configured to acquire a tomographic image of the subject, and a polarization adjustment member disposed in a common optical path of a portion of an optical system in the planar image acquisition unit and a portion of an optical system in the tomographic image acquisition unit and configured to adjust polarization states of a measuring beam for the planar image and a measuring beam for the tomographic image.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to an imaging apparatus configured tocapture of an image of a subject.

2. Description of the Related Art

An optical coherence tomography (OCT) technique using interference ofmulti-wavelength light enables acquisition of a high-resolutiontomographic image of a sample (in particular, a fundus of the eye).

In recent years, an ophthalmologic OCT apparatus can acquire, inaddition to a normal OCT image of a shape of a fundus tissue, apolarization-sensitive OCT image using a polarization parameter (i.e.,retardation and orientation), which is an optical characteristic of thefundus tissue.

The polarization-sensitive OCT (PS-OCT) can form thepolarization-sensitive OCT image using the polarization parameter to beformed, and perform distinguishing and segmentation of the fundustissue. PS-OCT uses the fact that some layers in the retina (or fundus)of an eye reflect polarized light differently from other layers.International Publication No. WO 2010/122118 A1 discusses apolarization-sensitive OCT which employs a light beam that has beenmodulated to a circularly-polarized beam as a measuring beam forexamining the sample. Detection is then performed by splitting theinterference beam into two linearly-polarized beams perpendicular toeach other, so that the polarization-sensitive OCT image is generatedwith different layers in the fundus being imaged differently dependingon their interaction with the polarized light.

It is desirable that the imaging apparatus is capable of capturing apolarization-sensitive scanning laser ophthalmoscope (SLO) image inaddition to the polarization-sensitive OCT image. In such an imagingapparatus, if a polarization-sensitive OCT optical system and apolarization-sensitive SLO optical system are separately provided,polarization states generated in an image acquired by thepolarization-sensitive OCT optical system and an image acquired by thepolarization-sensitive SLO optical system may be uneven.

SUMMARY OF THE INVENTION

The present invention is directed to comparatively reducing variation inthe polarization states generated in an image acquired by apolarization-sensitive OCT optical system and an image acquired by apolarization-sensitive SLO optical system.

According to an aspect of the present invention, an imaging apparatusincludes a planar image acquisition unit configured to acquire a planarimage of a subject, a tomographic image acquisition unit configured toacquire a tomographic image of the subject, and a polarizationadjustment member disposed in a common optical path of a portion of anoptical system in the planar image acquisition unit and a portion of anoptical system in the tomographic image acquisition unit and configuredto adjust polarization states of a measuring beam for the planar imageand a measuring beam for the tomographic image.

According to an exemplary embodiment of the present invention, animaging apparatus including a polarization adjustment member isprovided. The polarization adjustment member is disposed in a commonoptical path of a portion of the polarization-sensitive OCT opticalsystem and a portion of polarization-sensitive SLO optical system foradjusting the polarization states of the measuring beams of both opticalsystems. As a result, a variation in the polarization states generatedin an image acquired by the polarization-sensitive OCT optical systemand an image acquired by the polarization-sensitive SLO optical systemcan be comparatively reduced.

Further features and aspects of the present invention will becomeapparent from the following detailed description of exemplaryembodiments with reference to the attached drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated in and constitute apart of the specification, illustrate exemplary embodiments, features,and aspects of the invention and, together with the description, serveto explain the principles of the invention.

FIG. 1 is a schematic diagram illustrating an image processing apparatusaccording to an exemplary embodiment of the present invention.

FIGS. 2A, 2B, 2C, 2D, and 2E illustrate examples of images generated bya signal processing unit.

FIG. 3 is a flowchart illustrating a process according to the presentexemplary embodiment.

FIG. 4 illustrates a display example of a display screen on a displayunit in the image processing apparatus according to the presentexemplary embodiment.

FIG. 5 illustrates a display example of the display screen on thedisplay unit in the image processing apparatus according to the presentexemplary embodiment.

FIG. 6 illustrates a display example of the display screen on thedisplay unit in the image processing apparatus according to the presentexemplary embodiment.

FIG. 7 illustrates a display example of the display screen on thedisplay unit in the image processing apparatus according to the presentexemplary embodiment.

FIG. 8 illustrates a display example of the display screen on thedisplay unit in the image processing apparatus according to the presentexemplary embodiment.

FIG. 9 illustrates a display example of the display screen on thedisplay unit in the image processing apparatus according to the presentexemplary embodiment.

FIG. 10 illustrates an example of a two-dimensional layer thickness mapdisplayed on the display unit in the image processing apparatusaccording to the present exemplary embodiment.

DESCRIPTION OF THE EMBODIMENTS

Various exemplary embodiments, features, and aspects of the inventionwill be described in detail below with reference to the drawings.

An imaging apparatus according to an exemplary embodiment of the presentinvention is applicable to a subject such as a subject's eye, skin, andan internal organ. Further, the imaging apparatus according to thepresent exemplary embodiment may be an ophthalmologic apparatus or anendoscope.

FIG. 1 is a schematic diagram illustrating an ophthalmologic apparatus,which is an example of the imaging apparatus according to the presentexemplary embodiment. At least a portion of a signal processing unit 190to be described below may be considered as an image processingapparatus. In such a case, the ophthalmologic apparatus may beconsidered as an ophthalmologic system, or the imaging system may beconsidered as an imaging system.

Referring to FIG. 1, the ophthalmologic apparatus includes apolarization-sensitive OCT (PS-OCT) 100, a polarization-sensitivescanning laser ophthalmoscope (PS-SLO) 140, an anterior segment imagingunit 160, an internal fixation lamp 170, and a control unit 200.

The ophthalmologic apparatus is aligned by lighting and causing thesubject's eye to gaze at the internal fixation lamp 170, and using theimage of the anterior segment of the subject captured by the anteriorsegment imaging unit 160. After completing the alignment, the PS-OCT 100and the PS-SLO 140 perform imaging of the fundus.

The configuration of the PS-OCT 100 will be described below.

A light source 101 made of a super luminescent diode (SLD), i.e., alow-coherent light source, emits light having a central wavelength of850 nm and a bandwidth of 50 nm. Any light source that can emit lowcoherent light, such as an amplified spontaneous emission (ASE) lightsource, may be used as the light source 101.

The light emitted from the light source 101 is guided by a polarizationmaintaining (PM) fiber 102 and a polarization controller 103 to a fibercoupler 104 having a polarization preserving function. The beam is thensplit into a measuring beam (hereinafter referred to as a “measuringbeam for a tomographic image”, or an “OCT measuring beam”) and areference beam corresponding to the measuring beam.

The polarization controller 103 adjusts the polarization state of thebeam emitted from the light source 101, and adjusts the beam to alinearly-polarized beam. A branching ratio of the fiber coupler 104 is90 (reference beam): 10 (measuring beam).

The measuring beam is output from a collimator 106 via a PM fiber 105 asa parallel beam. The output measuring beam reaches a dichroic mirror 111via an X scanner 107, lenses 108 and 109, and a Y scanner 110. The Xscanner 107 includes a galvano mirror that scans the measuring beam in ahorizontal direction on a fundus Er, and the Y scanner 110 includes agalvano mirror that scans the measuring beam in a vertical direction onthe fundus Er. The X scanner 107 and the Y scanner 110 are controlled bya drive control unit 180, and are capable of scanning the measuring beamin a desired range on the fundus Er. The range in which the measuringbeam is scanned on the fundus may be considered as an acquisition rangeof the tomographic image, an acquisition position of the tomographicimage, and an irradiation position of the measuring beam. Further, the Xscanner 107 and the Y scanner 110 are examples of a scanning unit forPS-OCT, and may be configured as a common XY scanner. The dichroicmirror 111 reflects light having wavelengths of 800 nm to 900 nm, andtransmits light of other wavelengths.

The measuring beam reflected off the dichroic mirror 111 passes through,via a lens 112, a λ/4 polarizing plate 113 arranged to be inclined at anangle of 45° from a P-polarization to an S-polarization with respect toan optical axis as a rotational axis. The phase of the beam is thusshifted by 90°, and is polarized to a circularly-polarized beam. The λ/4polarizing plate 113 is an example of a polarization adjustment memberfor the measuring beam for adjusting the polarization state of themeasuring beam. If a PS-SLO optical system to be described below is tobe applied, the λ/4 polarizing plate 113 may be disposed in a commonoptical path between a portion of the PS-OCT optical system and aportion of the PS-SLO optical system. As a result, variation in thepolarization states generated in the images acquired by the PS-OCToptical system and the PS-SLO optical system can be comparativelyreduced. In such a case, the scanning unit for the PS-SLO and thescanning unit for the PS-OCT are arranged in mutually-conjugatepositions, and may be arranged to be conjugate with a pupil in thesubject's eye. The inclination of the λ/4 polarizing plate 113 is anexample of a state of the λ/4 polarizing plate 113, and is an angle froma predetermined position in the case where the optical axis of apolarizing beam splitting surface of a fiber coupler 123 including apolarizing beam splitter is the rotating axis.

Further, the λ/4 polarizing plate 113 may be inserted and removed fromthe optical path. For example, the λ/4 polarizing plate 113 may bemechanically configured to rotate around the optical axis or an axisparallel to the optical axis as the rotational axis. As a result, acompact apparatus capable of easily switching between the SLO opticalsystem and the PS-SLO optical system can be realized. Further, a compactapparatus capable of easily switching between the OCT optical system andthe PS-OCT optical system can be realized.

The beam incident on the subject's eye is thus polarized to acircularly-polarized beam by arranging the λ/4 polarizing plate 113 tobe inclined at an angle of 45°. However, the beam may not become acircularly-polarized beam on the fundus Er due to the characteristic ofthe subject's eye. To solve such a problem, the drive control unit 180can perform control to finely adjust the inclination of the λ/4polarizing plate 113.

A focus lens 114 mounted on a stage 116 focuses, on layers in a retinain the fundus Er via an anterior segment Ea of the subject's eye, themeasuring beam polarized to a circularly-polarized beam. The measuringbeam irradiating the fundus Er is reflected and scattered by each layerin the retina, and returns to the fiber coupler 104 via theabove-described optical path.

On the other hand, the reference beam branched by the fiber coupler 104is output as a parallel beam from a collimator 118 via a PM fiber 117.The output reference beam is polarized by a λ/4 polarizing plate 119arranged to be inclined at an angle of 22.5° from the P-polarization tothe S-polarization with the optical axis as the rotational axis,similarly as the measuring beam. The λ/4 polarizing plate 119 is anexample of the polarization adjustment member for the reference beam foradjusting the polarization state of the reference beam. The referencebeam is reflected via a dispersion compensation glass 120 by a mirror122 mounted on a coherence gate stage 121, and returns to the fibercoupler 104. The reference beam passes through the λ/4 polarizing plate119 twice, so that the linearly-polarized beam returns to the fibercoupler 104.

The coherence gate stage 121 is controlled by the drive control unit 180to deal with differences in an axial length of the subject's eye. Thecoherence gate is the position corresponding to an optical path lengthof the reference beam in the optical path of the measuring beam.According to the present exemplary embodiment, the optical path lengthof the reference beam is changeable. However, it is not limited thereto,as long as the difference in the optical path lengths of the measuringbeam and the optical beam can be changed.

The return beam and the reference beam that have returned to the fibercoupler 104 are combined into an interference beam (also referred to asa combined beam). The interference beam becomes incident on the fibercoupler 123 including the polarizing beam splitter, and is split at thebranching ratio of 50:50 into a P-polarized beam and an S-polarized beamof different polarization directions.

The P-polarized beam is dispersed by a grating 131 via a PM fiber 124and a collimator 130, and is received by a lens 132 and a line camera133. The S-polarized beam is similarly dispersed by a grating 127 via aPM fiber 125 and a collimator 126, and is received by a lens 128 and aline camera 129. The gratings 127 and 131 and the line cameras 129 and133 are arranged to match the direction of each polarization direction.

The beam received by each of the line cameras 129 and 133 is output asan electrical signal corresponding to the light intensity. The signalprocessing unit 190, which is an example of a tomographic imagegeneration unit, then receives the output electrical signals.

The inclinations of the λ/4 polarizing plates 113 and 119 can beautomatically adjusted based on the inclination of the polarizing beamsplitter surface of the polarizing beam splitter. The inclinations ofthe λ/4 polarizing plates 113 and 119 can also be automatically adjustedwith respect to a line connecting centers of an optic disk and a maculain the fundus. In such a case, it is desirable for an inclinationdetection unit (not illustrated) to detect the inclinations of the λ/4polarizing plates 113 and 119. The inclination detection unit can detectthe current inclination and detect whether the inclination has reached apredetermined inclination. Further, the inclinations of the λ/4polarizing plates 113 and 119 can be detected based on the intensity ofthe received light, and the inclinations can be adjusted so that apredetermined intensity is reached. Furthermore, an object indicatingthe inclination may be displayed on a graphical user interface (GUI),and the user may adjust the inclination using a mouse. Moreover, asimilar result can be acquired by adjusting a polarizing beam splitterand the λ/4 polarizing plates 113 and 119 based on the verticaldirection as a polarization basis.

The configuration of the PS-SLO 140 will be described below.

According to the present exemplary embodiment, a light source 141, i.e.,a semiconductor laser, emits a light beam having a central wavelength of780 nm. The measuring beam emitted from the light source 141(hereinafter referred to as a measuring beam for a fundus image, or anSLO measuring beam) is polarized via a PM fiber 142 by a polarizingcontroller 145 to a linearly-polarized beam, and is output from acollimator 143 as a parallel beam. The output measuring beam then passesthrough a perforated portion of a perforated mirror 144, and reaches,via a lens 155, a dichroic mirror 154 via an X scanner 146, lenses 147and 148, and a Y scanner 149. The X scanner 146 includes a galvanomirror that scans the measuring beam in the horizontal direction on thefundus Er, and the Y scanner 149 includes a galvano mirror that scansthe measuring beam in the vertical direction on the fundus Er. The Xscanner 146 and the Y scanner 149 are controlled by the drive controlunit 180, and are capable of scanning the measuring beam in the desiredrange on the fundus Er. Further, the X scanner 146 and the Y scanner 149are examples of a scanning unit for the PS-SLO, and may be configured asa common XY scanner. The dichroic mirror 154 reflects light havingwavelengths of 760 nm to 800 nm, and transmits light of otherwavelengths.

The linearly-polarized measuring beam reflected by the dichroic mirror154 reaches the fundus Er via the optical path similar to that of thePS-OCT 100.

The measuring beam irradiating the fundus Er is reflected and scatteredby the fundus Er, and reaches the perforated mirror 144 via theabove-described optical path. The beam reflected by the perforatedmirror 144 is then split by a polarizing beam splitter 151 via the lens150 into beams of different polarization directions (i.e., according tothe present exemplary embodiment, split into a P-polarized beam and anS-polarized beam). The split beams are received by avalanche photodiodes(APD) 152 and 153, converted into electrical signals, and received bythe signal processing unit 190, i.e., an example of the fundus imagegeneration unit.

The position of the perforated mirror 144 is conjugate with the positionof the pupil in the subject's eye. The perforated mirror 144 reflectsthe light that has passed through a peripheral region of the pupil amongthe light reflected and scattered by the fundus Er irradiated with themeasuring beam.

According to the present exemplary embodiment, both the PS-OCT and thePS-SLO use the PM fiber. However, a similar configuration and effect maybe acquired by using a single mode fiber (SMF) in the case where thepolarizing controller controls polarization.

The anterior segment imaging unit 160 will be described below.

The anterior segment imaging unit 160 irradiates the anterior segment Eausing an irradiation light source 115 including light emitting diodes(LED) 115-a and 115-b, which emit irradiation light having a wavelengthof 1000 nm. The light reflected by the anterior segment Ea reaches adichroic mirror 161 via the lens 114, the polarizing plate 113, the lens112, and the dichroic mirrors 111 and 154. The dichroic mirror 161reflects light having wavelengths of 980 nm to 1100 nm, and transmitslight of other wavelengths. The light reflected by the dichroic mirror161 is then received by an anterior segment camera 165 via lenses 162,163, and 164. The light received by the anterior segment camera 165 isconverted into an electrical signal and is received by the signalprocessing unit 190.

The internal fixation lamp 170 will be described below.

The interior fixation lamp 170 includes an interior fixation lampdisplay unit 171 and a lens 172. A plurality of LEDs arranged in amatrix shape is used as the interior fixation lamp display unit 171. Alighting position of the LED is changed by control performed by thedrive control unit 180 according to a region to be imaged. The lightemitted from the interior fixation lamp display unit 171 is guided tothe subject's eye via the lens 172. The interior fixation lamp displayunit 171 emits light having a wavelength of 520 nm, and the drivecontrol unit 180 displays a desired pattern.

A control unit 200 for controlling the entire apparatus according to thepresent exemplary embodiment will be described below.

The control unit 200 includes the drive control unit 180, the signalprocessing unit 190, a display control unit 191, and a display unit 192.

The drive control unit 180 controls each unit as described above.

The signal processing unit 190 generates images based on the signalsoutput from the line cameras 129 and 133, the APD 152 and 153, and theanterior segment camera 165, analyzes the generated images, andgenerates visualization information of the analysis results. The imagegeneration process will be described in detail below.

The display control unit 191 displays, on a display screen in thedisplay unit 192, the images generated by a tomographic image generationunit and a fundus image generation unit and acquired by a fundus imageacquisition unit (not illustrated) and a tomographic image acquisitionunit (not illustrated). The display unit 192 may be a liquid crystaldisplay. The image data generated by the signal processing unit 190 maybe transmitted to the display control unit 191 via wired or wirelesscommunication. In such a case, the display control unit 191 may beconsidered as the image processing apparatus. Further, the fundus imageacquisition unit may include the SLO optical system, and the tomographicimage acquisition unit may include the OCT optical system, as theimaging system. According to the present exemplary embodiment, if thesubject is other than the subject's eye, the fundus image (i.e., afundus intensity image) may be indicated as a planar image (i.e., aplane intensity image), and the fundus image acquisition unit as aplanar image acquisition unit.

The display unit 192 displays display forms indicating various types ofinformation to be described below based on control performed by thedisplay control unit 191. Image data from the display control unit 191may be transmitted to the display unit 192 via wired or wirelesscommunication. Further, the display unit 192 is included in the controlunit 200. However, it is not limited thereto, and the display unit 192may be separated from the control unit 200. Furthermore, a tablet, whichis an example of a portable device, configured by integrating thedisplay control unit 191 and the display unit 192 may be used. In such acase, it is desirable to include a touch panel function in the displayunit, so that a user can operate the touch panel to move the displayposition of the images, enlarge and reduce the images, and change theimages to be displayed.

Image generation and image analysis processes performed in the signalprocessing unit 190 will be described below.

The signal processing unit 190 performs, on interference signals outputfrom each of the line cameras 129 and 133, reconfiguration processingemployed in a common spectral domain (SD-) OCT. The signal processingunit 190 thus generates a tomographic image corresponding to a firstpolarized beam and a tomographic image corresponding to a secondpolarized beam, i.e., two tomographic images based on each polarizationcomponent.

More specifically, the signal processing unit 190 performs fixed patternnoise cancellation on the interference signals. The fixed pattern noisecancellation is performed by averaging a plurality of A-scan signalsthat has been detected and thus extracting the fixed pattern noise, andsubtracting the extracted fixed pattern noise from the inputinterference signal.

The signal processing unit 190 then transforms the wavelength of theinterference signal to a wave number, and performs Fourier transform, sothat a tomographic signal indicating the polarization state isgenerated.

The signal processing unit 190 performs the above-described process forthe interference signals of the two polarization components, and thusgenerates the two tomographic images.

Further, the signal processing unit 190 aligns the signals output fromthe APD 152 and 153 in synchronization with driving of the X scanner 146and the Y scanner 149. The signal processing unit 190 thus generates afundus image corresponding to the first polarized beam and a fundusimage corresponding to the second polarized beam, i.e., two fundusimages based on each polarization component.

Furthermore, the signal processing unit 190 generates a tomographicintensity image from the above-described two tomographic signals.

More specifically, the tomographic intensity image is basically the sameas the tomographic image in the conventional OCT. A pixel value r of thetomographic intensity image is calculated from tomographic signals A_(H)and A_(V) acquired from each of the line cameras 129 and 133 usingequation (1).r=√{square root over (A_(H) ² +A _(V) ²)}  (1)

Moreover, the signal processing unit 190 similarly generates a fundusintensity image from the two fundus images.

FIG. 2A illustrates an example of the intensity image of the optic disk.

When the λ/4 polarizing plate 113 is removed from the optical path, thedisplay control unit 191 may display, on the display unit 192, thetomographic intensity image acquired employing the conventional OCTtechnique, or the fundus intensity image acquired employing theconventional SLO technique.

Further, the signal processing unit 190 generates a retardation imagefrom the tomographic images of the polarization components that areperpendicular to each other.

A value δ of each pixel in the retardation image is a value indicating aratio of the effects received by the vertical polarization component andthe horizontal polarization component in the subject's eye, at theposition of each pixel configuring the tomographic image. The value δ iscalculated from each of the tomographic signals A_(H) and A_(V) usingequation (2).

$\begin{matrix}{\delta = {{arc}\;{\tan\left\lbrack \frac{A_{V}}{A_{H}} \right\rbrack}}} & (2)\end{matrix}$

FIG. 2B illustrates an example of the retardation image of the opticdisk generated as described above. The retardation image can be acquiredby calculating equation (2) for each B-scan image. As described above,the retardation image is a tomographic image indicating the differenceof the effect received by the two polarized beams in the subject's eye.Referring to FIG. 2B, the values indicating the above-described ratioare displayed as a color tomographic image. A darker-shaded portionindicates that the value of the ratio is small, and a lighter-shadedportion indicates that the value of the ratio is large. As a result,generating the retardation image enables recognizing a layer in whichthere is birefringence. For further details, refer to “Erich. Götzingeret al., Optics Express 13(25_(—): 1021710229, Dec. 12, 2005, OpticalSociety of America, Washington D.C.”.

Furthermore, the signal processing unit 190 can similarly generate aretardation image in a planar direction of the fundus based on theoutputs from the APD 152 and 153.

The signal processing unit 190 generates a retardation map from theretardation images acquired with respect to a plurality of B-scanimages.

More specifically, the signal processing unit 190 detects a retinalpigment epithelium (RPE) in each B-scan image. Since the RPE cancelspolarization, the signal processing unit 190 searches for a retardationdistribution of each A-scan along the depth direction in the range froman inner limiting membrane (ILM) without including the RPE. The signalprocessing unit 190 then sets a maximum value of the retardation as arepresentative value of the retardation in the A-scan.

The signal processing unit 190 performs the above-described process onall retardation images, and thus generates the retardation map.

FIG. 2C illustrates an example of the retardation map of the optic disk.Referring to FIG. 2C, the darker-shaded portion indicates that the valueof the ratio is small, and the lighter-shaded portion indicates that thevalue of the ratio is large. The layer having birefringence in the opticdisk is a retinal nerve fiber layer (RNFL), and the retardation mapillustrates the value indicating the ratio caused by the birefringencein the RNFL and the thickness of the RNFL. As a result, the valueindicating the ratio becomes large where the RNFL is thick, and becomessmall where the RNFL is thin. The thickness of the RNFL for the entirefundus thus becomes recognizable using the retardation map, and can beused in the diagnosis of glaucoma.

The signal processing unit 190 performs linear approximation of thevalue of the retardation 5 in the range of ILM to RNFL in each A scanimage of the previously generated retardation image. The signalprocessing unit 190 then determines the acquired slope as thebirefringence at the position on the retina in the A-scan image. Inother words, since retardation is a product of a distance and thebirefringence in the RNFL, a linear relation is acquired by plotting thedepth and the value of the retardation in each A-scan image. As aresult, linear approximation is performed on the plot using a leastsquare method, and the acquired slope becomes the value of thebirefringence in the RNFL in the A-scan image. The signal processingunit 190 performs the above-described process on all of the acquiredretardation images, and generates the map representing thebirefringence.

FIG. 2D illustrates an example of the birefringence map of the opticdisk. The birefringence map directly maps the values of thebirefringence. As a result, when a fibrous architecture of the RNFLchanges even if the thickness of the RNFL does not change, the changecan be visualized as the change in the birefringence.

The signal processing unit 190 calculates a Stokes vector S for eachpixel from the acquired tomographic signals A_(H) and A_(V), and a phasedifference ΔΦ between the tomographic signals A_(H) and A_(V), usingequation (3).

$\begin{matrix}{S = {\begin{pmatrix}I \\Q \\U \\V\end{pmatrix} = \begin{pmatrix}{A_{H}^{2} + A_{V}^{2}} \\{A_{H}^{2} - A_{V}^{2}} \\{2A_{H}A_{V}\cos\;{\Delta\phi}} \\{2A_{H}A_{V}\sin\;\Delta\;\phi}\end{pmatrix}}} & (3)\end{matrix}$In such a case, ΔΦ is calculated from phases Φ_(H) and Φ_(V) of eachsignal acquired when calculating the two tomographic images, asΔΦ=Φ_(V)−Φ_(H).

The signal processing unit 190 then sets, in each B-scan image, a windowof the size that is proximately 70 μm in a main scanning direction ofthe measuring beam and 18 μm in a depth direction. The signal processingunit 190 then averages each element of the Stokes vector calculated foreach pixel by a number C within each window, and calculates a degree ofpolarization uniformity (DOPU) within the window using equation (4).DOPU=√{square root over (Q _(m) ² +U _(m) ² +V _(m) ²)}  (4)In equation (4), Q_(m), U_(m), and V_(m) are values acquired byaveraging the elements Q, U, and V in the Stokes vector within eachwindow. The signal processing unit 190 performs the above-describedprocess for all windows in the B-scan images, and generates a DOPU imageof the optic disk as illustrated in FIG. 2E. As described above, theDOPU image is a tomographic image indicating the degree of polarizationuniformity of the two types of polarization.

DOPU is a value indicating the uniformity of polarization, and becomesclose to “1” when polarization is preserved, and smaller than “1” whenpolarization is cancelled or not preserved. Since the RPE in thestructure of the retina cancels the polarization state, the value of theDOPU in the portion corresponding to the RPE in the DOPU image becomeslower than the values in the other portions. Referring to FIG. 2E, thelighter-shaded portion indicates the RPE. The DOPU image visualizes thelayer such as the RPE that cancels polarization, so that the image ofthe RPE can be firmly acquired as compared to the change in theintensity even when the RPE is deformed due to a disease.

Further, the signal processing unit 190 can similarly generate a DOPUimage in the planar direction of the fundus based on the outputs fromthe APD 152 and 153.

According to the present exemplary embodiment, the above-describedtomographic images corresponding to the first and second polarizedbeams, the retardation image, and the DOPU image will be referred to astomographic images indicating the polarization state. Further, accordingto the present exemplary embodiment, the above-described retardation mapand the birefringence map will also be referred to as fundus imagesindicating the polarization state.

The signal processing unit 190 uses the above-described intensity imageto perform segmentation of the tomographic image.

More specifically, the signal processing unit 190 applies, to thetomographic image to be processed, a median filter as a type ofsmoothing filter, and a Sobel filter as a type of an edge detectionmethod. The signal processing unit 190 thus generates respective images(hereinafter referred to as a median image and a Sobel image). Thesignal processing unit 190 then generates a profile for each A-scan fromthe generated median image and Sobel image. The signal processing unit190 generates the profile of the intensity value from the median imageand the profile of a gradient from the Sobel image. The signalprocessing unit 190 detects peaks in the profiles generated from theSobel image. Further, signal processing unit 190 extracts a boundary ofeach layer in the retina by referring to the profiles of the medianimage corresponding to regions before and after the detected peaks andthe regions between the detected peaks.

Further, the signal processing unit 190 measures each layer thickness inthe direction of the A-scan line, and generates a layer thickness map ofeach layer.

The operation performed in the image processing apparatus according tothe present exemplary embodiment will be described below.

FIG. 3 is a flowchart illustrating the operation performed by the imageprocessing apparatus according to the present exemplary embodiment.

In step S101, the image processing apparatus and the subject's eyepositioned on the image processing apparatus are aligned. The processunique to the present exemplary embodiment with respect to performingalignment will be described below. Since alignment of a working distancein X, Y, and Z directions, focusing, and adjustment of the coherencegate are common, description will be omitted.

FIG. 4 illustrates a window 400 displayed on the display unit 192 whenperforming adjustment. Referring to FIG. 4, a display area 410, i.e., anexample of a first display area, displays a fundus image 411 imaged bythe PS-SLO 140 and generated by the signal processing unit 190. A frame412 indicating an imaging range of the PS-OCT 100 is superimposed on thefundus image 411.

An operator sets the imaging range under control of the drive controlunit 180, by clicking and dragging an instruction device (notillustrated), such as a mouse, and designating by a cursor displayed onthe window 400. In other words, the operator designates the frame 412using the cursor, and moves the frame 412 by the dragging operation. Asa result, the drive control unit 180 controls a drive angle of a scannerand sets the imaging range. According to the present exemplaryembodiment, the mouse includes a sensor for detecting a movement signalwhen the user manually moves the mouse in two directions, left and rightmouse buttons for detecting that the user has pressed the button, and awheel mechanism between the two mouse buttons which is movable in frontand back and left to right directions. Further, the display unit mayinclude a touch panel function, and the operator may designate theacquisition position on the touch panel.

The adjustment of the λ/4 polarizing plate 113 will be described below.

Referring to FIG. 4, indicators 413 and 414 are displayed for adjustingthe angle of the λ/4 polarizing plate 113. When the user instructs usingthe instruction device, the angle of the λ/4 polarizing plate 113 isadjusted based on control of the drive control unit 180. The indicator413 is for instructing adjustment in a counterclockwise direction, andthe indicator 414 is for instructing adjustment in a clockwisedirection. A numerical value displayed besides the indicators 413 and414 indicates the current angle of the λ/4 polarizing plate 113. Thedisplay control unit 191 may display the indicator for adjusting theangle of the λ/4 polarizing plate 119 side by side with the indicator413 on the display unit 192, or in place of the indicator 413.

The operator gives, using the cursor by operating on the mouse, aninstruction so that the intensities of the tomographic images of eachpolarized beam respectively displayed on a display area 430, i.e., anexample of a third display area, and a display area 440, i.e., anexample of a fourth display area, become the same. A peak intensityvalue may be displayed along with tomographic images 431 and 441 of eachpolarized beam, or a waveform of each interference signal may bedisplayed, so that the operator performs adjustment while viewing thepeak intensity value or the waveform. The tomographic images 431 and 441of each polarized beam are examples of tomographic images correspondingto the first polarized beam and the second polarized beam, respectively.It is desirable to display a type of each image on the tomographicimages 431 and 441 of each polarized beam (or tomographic images 531 and541 to be described below). For example, a letter “P” indicating theP-polarized beam and a letter “S” indicating the S-polarized beam may bedisplayed. As a result, such a display prevents the user frommisrecognizing the image. The letters may be displayed above or besidesthe image instead of being superimposed on the image, as long as thedisplay is arranged to be associated with the image.

It is not necessary at this point for a display area 420, i.e., anexample of a second display area, to display any information. If autoadjustment is to be performed, the current adjustment state, such as amessage informing “adjusting λ/4 polarizing plate”, may be displayed onthe display area 420. Further, a display indicating patient informationsuch as a left eye or a right eye, or image capturing information suchas an image capturing mode may be performed on the window 400.Furthermore, it is desirable to repeatedly insert and remove the λ/4polarizing plate 113 with respect to the optical path for alternatelyacquiring the fundus intensity image and the tomographic imageindicating the polarization state. As a result, the display control unit191 even in a minimum-sized ophthalmologic apparatus can display thefundus intensity image on the display area 410 and the tomographic imageindicating the polarization state on the display area 420.

It is desirable to perform adjustment in the following order: alignmentadjustment using the anterior segment image or a luminescent spot in acornea; focus adjustment using the fundus image indicating thepolarization state; coherence gate adjustment using the tomographicimage indicating the polarization state; and adjustment of the λ/4polarizing plate. Further, it is desirable to determine the acquisitionposition of the tomographic image indicating the polarization statebefore adjusting the coherence gate using the tomographic imageindicating the polarization state. However, the acquisition position maybe determined in an initial setting for acquiring a center region of thefundus image indicating the polarization state. Adjustment can thus besimply performed to accurately acquire the tomographic image indicatingthe polarization state that is finer and corresponding to a narrowerrange as compared to the fundus image indicating the polarization state.In such a case, the λ/4 polarizing plate may be automatically adjustedin response to completion of adjustment of the coherence gate, or inresponse to input of a signal for acquiring the image indicating thepolarization state. Further, the λ/4 polarizing plate may be previouslyadjusted on an initial setting screen when activating the ophthalmologicapparatus, so that the λ/4 polarizing plate is not required to beadjusted for each image capturing.

Furthermore, if the λ/4 polarizing plate can be inserted and removedwith respect to the optical path, it is desirable to perform adjustmentin the following order: alignment adjustment using the anterior segmentimage or the luminescent spot in the cornea; focus adjustment using theSLO fundus image; coherence gate adjustment using the OCT tomographicimage; and adjustment of the λ/4 polarizing plate after inserting theλ/4 polarizing plate in the optical path. Adjustment can thus beperformed before acquiring the image indicating the polarization state,using the normal SLO fundus image and the OCT tomographic image that theuser is intuitively used to. The coherence gate may also be adjustedusing the tomographic image indicating the polarization state of thePS-OCT by inserting the λ/4 polarizing plate after performing focusadjustment. In such a case, the λ/4 polarizing plate may beautomatically inserted in response to completion of adjustment of thecoherence gate, or in response to input of the signal for acquiring theimage indicating the polarization state.

Moreover, the focus may be finely adjusted using the OCT tomographicimage after coarsely adjusting the focus using the SLO fundus image.

Further, all of such adjustments may be automatically performed in theabove-described order, or by the user adjusting the cursor to a slidercorresponding to each type of adjustment displayed on the display unitand performing dragging. Furthermore, if the λ/4 polarizing plate is tobe inserted or removed, an icon instructing inserting or removing theλ/4 polarizing plate with respect to the optical path may be displayedon the display unit.

In step S102, step S103, and step S104 illustrated in FIG. 3, each ofthe light sources 101 and 141 emits the measuring beam. The line cameras129 and 133 and the APD 152 and 153 then receive the return beam, andthe signal processing unit 190 generates and analyzes each image asdescribed above.

The process for outputting the generated image and the analysis resultperformed in step S105 will be described below.

After the signal processing unit 190 completes generating and analyzingeach image, the display control unit 191 generates output informationbased on the result. The display control unit 191 then outputs to anddisplays on the display unit 192 the output information.

FIG. 5 illustrates a display example on the display unit 192 accordingto the present exemplary embodiment.

Referring to FIG. 5, a window 500 displayed on the display unit 192includes display areas 510, 520, 530, and 540.

The display area 510, i.e., an example of the first display area,displays a fundus image 511, and a rectangular frame 512 indicating theposition of the tomographic image is superimposed on the fundus image511. The fundus intensity image is displayed as the fundus image 511.However, the fundus image may be generated based on a polarizationsignal.

The display area 520, i.e., an example of the second display area,displays a tomographic image 521. Further, the display area 520 displaysbuttons 522, 523, 524, and 525, i.e., examples of a selection unit forselecting the type of the tomographic image to be displayed. The usermay select the type of the tomographic image from a menu instead ofusing the buttons 522, 523, 524, and 525. In the example illustrated inFIG. 5, the user has selected the button 522.

The display area 530, i.e., an example of a third display area, and thedisplay area 540, i.e., an example of a fourth display area,respectively display tomographic images 531 and 541 based on eachpolarization signal used in generating the tomographic image 521. Thedisplay areas 530 and 540 may also display each fundus image based oneach polarization signal from which the fundus image displayed on thedisplay area 510 has been generated, according to an instruction by theoperator via the menu.

It is desirable to display the tomographic intensity image 521, and aretardation image 621 and a DOPU image 721 to be described below, bysuperimposing the display form indicating the type of the image, such as“intensity”, “retardation”, and “DOPU” in characters. As a result, theuser can be prevented from misrecognizing the image. The type of imagemay be displayed above or besides the image instead of beingsuperimposed on the image, as long as the characters are arranged to beassociated with the image.

If the operator presses the button 523, the tomographic image displayedon the display area 520 can be changed to a retardation image 621 asillustrated in FIG. 6.

Referring to FIG. 6, the display areas 530 and 540 respectively displaythe tomographic images 531 and 541 similarly as in FIG. 5.

If the operator then presses the button 524, the tomographic imagedisplayed on the display area 520 can be changed to a DOPU image 721 asillustrated in FIG. 7.

Referring to FIG. 7, the display area 530 displays the intensity image521, and the display area 540 displays the retardation image 621. It isdesirable to provide a button for selecting the image for each displayarea. The user thus becomes capable of easily selecting the images to becompared, such as a plurality of tomographic images indicating differentpolarization states.

If the operator presses the button 525, the tomographic image displayedon the display area 520 can be changed to an image 821 indicating asegmentation result as illustrated in FIG. 8. Referring to FIG. 8, colorline segments indicating the layer boundaries are superimposed on thetomographic image and displayed in the image 821, and the RPE ishighlighted. The layer selected by the operator using the cursor ishighlighted.

The display area 540 displays a tomographic image 841, used inperforming segmentation, and buttons 842 and 843. If the operatorpresses the buttons 842 and 843, the intensity image 841 can be switchedto a graph 941, illustrated in FIG. 9, indicating the layer thickness ofthe highlighted layer.

Further, referring to FIG. 9, thickness information of the selectedlayer (e.g., a two-dimensional layer thickness map as illustrated inFIG. 10) may be displayed on the display area 530. Referring to FIG. 10,the thickness of the selected layer is expressed by a difference incolor. An integration image may be displayed in place of the thicknessof the selected layer illustrated in FIG. 10. The integration image maybe generated based on a specific layer or on the entire PS-OCT. Further,according to the present exemplary embodiment, the image to be displayedis changed according to the instruction of the operator. However, theinformation on the disease to be diagnosed, such as the name of thedisease, may be selected from the menu, and the image on which apriority order has been preset with respect to the disease may bedisplayed on each display area.

Furthermore, the display control unit 191 may display, on one of thedisplay areas in the display unit 192, the retardation map or thebirefringence map instead of the above-described images. Moreover, thedisplay control unit 191 may superimpose and display the retardation mapand the birefringence map on the fundus intensity image 511. In such acase, it is desirable to superimpose and display the retardation map orthe birefringence map on the area indicated by the frame 512.

As described above, according to the present exemplary embodiment, eachof the generated images can be efficiently presented to the operator.

Further, the operator can select the necessary images with easyoperation. In particular, the operation becomes easier by previouslyassociating the name of the disease with the image to be displayed.

Furthermore, polarization adjustment of the measuring beam can be easilyperformed.

According to the present exemplary embodiment, the positions of thedisplay areas in which the above-described images are displayed are notlimited thereto. For example, the fundus image may be displayed in theleft display area in the display screen. Further, the number of imagesto be displayed is not limited thereto. For example, the fundus imageand the tomographic image (i.e., two images) may be displayed side byside on the display screen when performing adjustment. The displaymethod may then be changed after performing image capturing, and aplurality of tomographic images indicating different polarization statesmay be displayed side by side on the display screen along with thefundus image. Furthermore, the order and the positions in which thebuttons 522, 523, 524, and 525 are arranged are not limited thereto.

Aspects of the present invention can also be realized by a computer of asystem or apparatus (or devices such as a CPU or MPU) that reads out andexecutes a program recorded on a memory device to perform the functionsof the above-described embodiment (s), and by a method, the steps ofwhich are performed by a computer of a system or apparatus by, forexample, reading out and executing a program recorded on a memory deviceto perform the functions of the above-described embodiment(s). For thispurpose, the program is provided to the computer for example via anetwork or from a recording medium of various types serving as thememory device (e.g., non-transitory computer-readable medium).

While the present invention has been described with reference toexemplary embodiments, it is to be understood that the invention is notlimited to the disclosed exemplary embodiments. The scope of thefollowing claims is to be accorded the broadest interpretation so as toencompass all modifications, equivalent structures, and functions.

This application claims priority from Japanese Patent Application No.2012-010280 filed Jan. 20, 2012, which is hereby incorporated byreference herein in its entirety.

What is claimed is:
 1. An imaging apparatus comprising: a planar imageacquisition unit configured to acquire a planar image of a subject; asplitting unit configured to split light generated by a light sourceinto a measuring beam for a tomographic image of the subject and areference beam; a tomographic image acquisition unit configured toacquire the tomographic image based on a combined beam obtained bycombining the reference beam and a return beam from the subjectirradiated with the measuring beam for the tomographic image; a branchunit configured to branch into an optical path of a measuring beam forthe planar image and an optical path of the measuring beam for thetomographic image, the branch unit being disposed closer to the subjectthan the splitting unit; and a polarization adjustment member configuredto adjust polarization states of the measuring beam for the planar imageand the measuring beam for the tomographic image, the polarizationadjustment member being disposed closer to the subject than the branchunit in a common optical path of the optical path of the measuring beamfor the planar image and the optical path of the measuring beam for thetomographic image.
 2. The imaging apparatus according to claim 1,further comprising a display control unit configured to cause a displayunit to display the planar image and the tomographic image side by side.3. The imaging apparatus according to claim 2, wherein the planar imageacquisition unit acquires a polarization-sensitive planar image of thesubject based on beams of different polarizations obtained by splittinga return beam from the subject irradiated with a measuring beam thepolarization state of which has been adjusted by the polarizationadjustment member, wherein the tomographic image acquisition unitacquires a polarization-sensitive tomographic image of the subject basedon beams of different polarizations obtained by splitting a beam intowhich a return beam from the subject irradiated with a measuring beamthe polarization state of which has been adjusted by the polarizationadjustment member and a reference beam corresponding to the measuringbeam have been combined, and wherein the display control unit causes thedisplay unit to display the polarization-sensitive planar image of thesubject and the polarization-sensitive tomographic image of the subjectside by side.
 4. The imaging apparatus according to claim 2, wherein thetomographic image acquisition unit acquires a tomographic intensityimage of the subject based on tomographic images corresponding to firstand second polarized beams from the subject, and wherein the displaycontrol unit causes the display unit to display the tomographicintensity image.
 5. The imaging apparatus according to claim 2, whereinthe planar image acquisition unit acquires a planar intensity image ofthe subject based on planar images corresponding to first and secondpolarized beams from the subject, and wherein the display control unitcauses the display unit to display the planar intensity image.
 6. Theimaging apparatus according to claim 1, wherein the subject is an eye.7. The imaging apparatus according to claim 1, further comprising adisplay control unit configured to cause a display unit to display theplanar image and the tomographic image side by side on a same screen ofthe display unit, wherein the tomographic image acquisition unitacquires, as the tomographic image, a tomographic intensity image of thesubject based on first and second polarized beams from the subject. 8.The imaging apparatus according to claim 1, further comprising a displaycontrol unit configured to cause a display unit to display the planarimage and the tomographic image side by side on a same screen of thedisplay unit, wherein the planar image acquisition unit acquires, theplanar image, a planar intensity image of the subject based on first andsecond polarized beams from the subject.
 9. The imaging apparatusaccording to claim 1, wherein the tomographic image acquisition unitacquires, as the tomographic image, a tomographic intensity image of thesubject based on first and second polarized beams from the subject; andwherein the planar image acquisition unit acquires, as the planar image,a planar intensity image of the subject based on first and secondpolarized beams from the subject.
 10. The imaging apparatus according toclaim 9, further comprising a display control unit configured to cause adisplay unit to display the acquired planar intensity image and theacquired tomographic intensity image.
 11. The imaging apparatusaccording to claim 1, further comprising a plurality of detection unitsconfigured to detect first and second polarized beams obtained bysplitting a combined beam obtained by combining a reference beam and areturn beam from the subject irradiated with the measuring beam for thetomographic image, and wherein the tomographic image acquisition unitacquires, as the tomographic image, a tomographic intensity image of thesubject based on the detected first and second polarized beams.
 12. Theimaging apparatus according to claim 1, further comprising a pluralityof detection units configured to detect first and second polarized beamsfrom the subject irradiated with the measuring beam for the planarimage, and wherein the planar image acquisition unit acquires, as theplanar image, a planar intensity image of the subject based on thedetected first and second polarized beams.
 13. The imaging apparatusaccording to claim 1, further comprising a plurality of detection unitsconfigured to detect first and second polarized beams obtained bysplitting a combined beam obtained by combining a reference beam and areturn beam from the subject irradiated with the measuring beam for thetomographic image, and wherein the tomographic image acquisition unitacquires, as the tomographic image, a polarization-sensitive tomographicimage of the subject based on the detected first and second polarizedbeams.
 14. The imaging apparatus according to claim 1, furthercomprising a plurality of detection units configured to detect first andsecond polarized beams from the subject irradiated with the measuringbeam for the planar image, and wherein the planar image acquisition unitacquires, as the planar image, a polarization-sensitive planar image ofthe subject based on the detected first and second polarized beams. 15.An imaging apparatus comprising: a plurality of detection unitsconfigured to detect first and second polarized beams from a subjectirradiated with a measuring beam for a polarization-sensitive planarimage of the subject; a planar image acquisition unit configured toacquire the polarization-sensitive planar image based on the detectedfirst and second polarized beams; a plurality of detection unitsconfigured to detect third and fourth polarized beams obtained bysplitting a combined beam obtained by combining a reference beam and areturn beam from the subject irradiated with a measuring beam for apolarization-sensitive tomographic image of the subject; a tomographicimage acquisition unit configured to acquire the polarization-sensitivetomographic image based on the detected third and fourth polarizedbeams; a branch unit configured to branch into an optical path of ameasuring beam for the polarization-sensitive planar image and anoptical path of the measuring beam for the polarization-sensitivetomographic image; and an optical member disposed closer to the subjectthan the branch unit in a common optical path of the optical path of themeasuring beam for the polarization-sensitive planar image and theoptical path of the measuring beam for the polarization-sensitivetomographic image.
 16. The imaging apparatus according to claim 15,wherein the optical member includes an objective lens.
 17. The imagingapparatus according to claim 15, wherein the subject is an eye.
 18. Theimaging apparatus according to claim 15, further comprising a displaycontrol unit configured to cause a display unit to display the acquiredpolarization-sensitive planar image and the acquiredpolarization-sensitive tomographic image side by side on a same screenof the display unit.
 19. The imaging apparatus according to claim 15,wherein the optical member includes a polarization adjustment member.20. An imaging apparatus comprising: a plurality of detection unitsconfigured to detect first and second polarized beams from a subjectirradiated with a measuring beam for a planar intensity image of thesubject; a planar image acquisition unit configured to acquire theplanar intensity image based on the detected first and second polarizedbeams; a plurality of detection units configured to detect third andfourth polarized beams obtained by splitting a combined beam obtained bycombining a reference beam and a return beam from the subject irradiatedwith a measuring beam for a tomographic intensity image of the subject;a tomographic image acquisition unit configured to acquire thetomographic intensity image based on the detected third and fourthpolarized beams; a branch unit configured to branch into an optical pathof the measuring beam for the planar intensity image and an optical pathof the measuring beam for the tomographic intensity image; and anoptical member disposed closer to the subject than the branch unit in acommon optical path of the optical path of the measuring beam for theplanar intensity image and the optical path of the measuring beam forthe tomographic intensity image.
 21. The imaging apparatus according toclaim 20, further comprising a display control unit configured to causea display unit to display the acquired planar intensity image and theacquired tomographic intensity image side by side on a same screen ofthe display unit.
 22. The imaging apparatus according to claim 20,wherein the optical member includes an objective lens.
 23. The imagingapparatus according to claim 20, wherein the optical member includes apolarization adjustment member.
 24. The imaging apparatus according toclaim 20, wherein the subject is an eye.